JP2016067720A - Ultrasonic diagnostic apparatus, ultrasonic image processor and ultrasonic image processing program - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an ultrasonic diagnostic apparatus and the like, which can reduce the time required for analysis and diagnosis using such as a tissue tracking imaging method and improve accuracy in analysis and diagnosis.SOLUTION: Volume data based on ultrasonic scanning to a three-dimensional region including at least a part of the heart is acquired, the three-dimensional shape of a first portion is acquired on the basis of the contour of the first portion in each of the plurality of cross-sectional images intersecting each other along the extension direction of the first portion corresponding to the blood inflow path to the heart chamber, the three-dimensional shape of a second portion is acquired on the basis of the contour of the second portion in the cross-sectional image along the extension direction of the second portion corresponding to the blood outflow path from the heart chamber, and a three-dimensional image indicating the shape of at least a part of the heart muscle including the first portion, second portion and heart chamber is generated by using the three-dimensional shape indicating the heart chamber and the three-dimensional shapes of the first portion and the second portion acquired by an acquisition part.SELECTED DRAWING: Figure 2

Description

  The present embodiment provides an ultrasonic diagnostic apparatus and an ultrasonic image that provide information useful for medical diagnosis by outputting local motion information of a tissue such as a myocardium (muscles constituting the heart) using an ultrasonic image. The present invention relates to a processing apparatus and an ultrasonic image processing program.

  Ultrasonic diagnostic equipment can obtain heart beats and fetal movements on a real-time display with a simple operation by simply touching the ultrasound probe from the body surface, and it can be repeatedly tested because it is highly safe. it can. In addition, it can be said that this is a simple diagnostic method in which the scale of the system is smaller than other diagnostic devices such as X-rays, CT, and MRI, and inspection can be easily performed while moving to the bedside. Ultrasound diagnostic devices used in this ultrasound diagnosis vary depending on the types of functions that they have, but small ones that can be carried with one hand have been developed. Thus, there is no influence of exposure, and it can be used in obstetrics and home medical care.

  In recent years, there is a tissue tracking imaging (TTI) method as a method for objectively and quantitatively evaluating the function of an object as a living tissue using such an ultrasonic diagnostic apparatus. By this TTI method, it is possible to provide a quantitative evaluation method using local wall motion indices such as strain and displacement using the tissue velocity. In the TTI method, it is necessary to input a three-dimensional boundary of an object in reference time phase volume data. As this input method, there is a technique in which a plurality of cross-sectional images are set in the volume data, the boundary of an object is traced on each two-dimensional image corresponding to each cross section, and a three-dimensional boundary is generated by interpolation processing between the cross sections. Are known. In this technique, for example, when an object is a myocardium of the left ventricle of the heart included in the ultrasound image and the three-dimensional boundary is input in the volume data of the reference time phase, the myocardial boundary in a plurality of short-axis cross sections of the left ventricle And a three-dimensional myocardial boundary is generated by interpolation processing of each cross section. If the target to be used for analysis is only the ventricle and the inflow part (for example, the mitral valve in the case of the left ventricle and the tricuspid valve in the case of the right ventricle) for flowing blood into the ventricle, By setting the position of the ultrasonic probe together, both are displayed relatively clearly even with only the short-axis cross-section in the prior art, and it is easy to set the myocardial boundary appropriately.

Japanese Patent No. 5276407

T.E. Cootes, et al., “Active shape models-Their training and application” CVIU. 1995.

  However, if the object used for analysis includes the ventricle and the inflow part, as well as the outflow part (for example, the pulmonary valve in the case of the right ventricle) for letting out blood from the ventricle, Although the visibility of one side can be sufficiently secured, the visibility of the other side cannot be sufficiently secured. As a result, the time required for analysis and diagnosis increases. In addition, since it is difficult to set the myocardial boundary appropriately, the accuracy of analysis and diagnosis cannot be sufficiently ensured.

  In view of the above circumstances, the object is to provide a sonic diagnostic apparatus, an ultrasonic image processing apparatus, and an ultrasonic image processing program capable of reducing the time required for analysis and diagnosis and improving the accuracy of analysis and diagnosis. is there.

  An ultrasonic diagnostic apparatus according to an embodiment includes a data acquisition unit that acquires volume data based on ultrasonic scanning on a three-dimensional region including at least a part of a heart, and a first part corresponding to a blood inflow route to a heart cavity The three-dimensional shape of the first part is acquired based on the outline of the first part in each of a plurality of cross-sectional images intersecting with each other along the extending direction of the first part, and the first part corresponding to the blood outflow route from the heart chamber is obtained. An acquisition unit that acquires a three-dimensional shape of the second part based on an outline of the second part in a cross-sectional image along the extending direction of two parts, a three-dimensional shape that indicates the heart chamber, and the acquisition part 3D showing the shape of at least a part of the myocardium including the first part, the second part, and the heart chamber using the three-dimensional shape of the first part and the second part acquired in Image students that generate images Comprising a part, a.

FIG. 1 is a block diagram illustrating a configuration of an ultrasonic diagnostic apparatus according to an embodiment. FIG. 2 is a block diagram of the motion information processing unit 29 according to this embodiment. FIG. 3 is an example of a flowchart in the case of performing tissue tracking imaging using the three-dimensional myocardial shape setting support function of the ventricle realized by the ultrasonic diagnostic apparatus 1 according to the present embodiment. FIGS. 4A and 4B are diagrams for explaining the first part setting process. FIGS. 5A, 5 </ b> B, and 5 </ b> C are diagrams for explaining the first part setting process. FIG. 6 is a diagram for explaining the setting process of the second part. FIGS. 7A, 7 </ b> B, and 7 </ b> C are diagrams for explaining the setting process of the second part. FIG. 8 is a diagram illustrating an example of the three-dimensional shape of the first part VI and the three-dimensional shape of the second part VO set on the volume data. FIG. 9 is a diagram illustrating an example of the three-dimensional myocardial shape VE of the ventricle including the three-dimensional shape of the first part VI and the three-dimensional shape of the second part VO. FIGS. 10A and 10B illustrate a process of deforming an ellipse and a circle on a cross-sectional image connected to the ventricle so that the three-dimensional shapes of the inflow portion and the outflow portion are smoothly connected. FIG. FIG. 11 is a diagram showing a modified example of the long-axis cross-sectional image used for setting the contour lines 50, 51, 52, and 53 of the myocardial region in the first part and the contour lines 60 and 61 of the myocardial region in the second part. It is.

  Hereinafter, embodiments will be described with reference to the drawings. In the following description, components having substantially the same function and configuration are denoted by the same reference numerals, and redundant description will be given only when necessary.

  FIG. 1 is a block diagram illustrating a configuration of an ultrasonic diagnostic apparatus according to an embodiment. As shown in the figure, the ultrasonic diagnostic apparatus 1 includes an ultrasonic probe 12, an input device 13, a monitor 14, an ultrasonic transmission unit 20, an ultrasonic reception unit 21, an input buffer 22, a B-mode processing unit 23, a color. Doppler processing unit 24, FFT Doppler processing unit 25, RAW data memory 26, volume data generation unit 27, motion information processing unit 29, image processing unit 28, display processing unit 30, control processor (CPU) 31, storage unit 32, interface A unit 33 is provided. Hereinafter, the function of each component will be described. The ultrasonic probe 12, the input device 13, the monitor 14, the ultrasonic transmission unit 20, the ultrasonic reception unit 21, the input buffer 22, the B-mode processing unit 23, the color Doppler processing unit 24, the FFT Doppler processing unit 25, and RAW data. The memory 26 and the volume data generation unit 27 constitute a data acquisition unit.

  The ultrasonic probe 12 is a device (probe) that transmits ultrasonic waves to a subject whose typical example is a living body, and receives reflected waves from the subject based on the transmitted ultrasonic waves. A plurality of piezoelectric vibrators (ultrasonic transducers), a matching layer, a backing material, and the like. The piezoelectric vibrator transmits an ultrasonic wave in a desired direction in the scan region based on a drive signal from the ultrasonic transmission unit 20, and converts a reflected wave from the subject into an electric signal. The matching layer is an intermediate layer provided in the piezoelectric vibrator for efficiently propagating ultrasonic energy. The backing material prevents ultrasonic waves from propagating backward from the piezoelectric vibrator. When ultrasonic waves are transmitted from the ultrasonic probe 12 to the subject, the transmitted ultrasonic waves are successively reflected by the discontinuous surface of the acoustic impedance of the body tissue and received by the ultrasonic probe 12 as an echo signal. The amplitude of this echo signal depends on the difference in acoustic impedance at the discontinuous surface that is to be reflected. Further, the echo when the transmitted ultrasonic pulse is reflected by the moving bloodstream undergoes a frequency shift due to the Doppler effect depending on the velocity component in the ultrasonic transmission / reception direction of the moving body. In the present embodiment, the ultrasonic probe 12 can acquire volume data, and is a two-dimensional array probe (probe in which a plurality of ultrasonic transducers are arranged in a two-dimensional matrix) or a mechanical 4D probe (super It is assumed that the probe is capable of performing ultrasonic scanning while mechanically rolling the acoustic transducer array in a direction orthogonal to the arrangement direction.

  The input device 13 is connected to the apparatus main body 11 and is used to incorporate various instructions, conditions, region of interest (ROI) setting instructions, various image quality condition setting instructions, etc. from the operator such as selection of an imaging mode into the apparatus main body 11. It has various switches, buttons, trackballs, mice, keyboards, etc.

  Based on the video signal from the display processing unit 30, the monitor 14 displays in-vivo morphological information and blood flow information acquired by the color Doppler mode as an image. Further, the monitor 14 displays an ultrasonic image reproduced by a color Doppler imaging method described later together with predetermined information in a predetermined form.

  The ultrasonic transmission unit 20 includes a trigger generation circuit, a delay circuit, a pulsar circuit, and the like (not shown). The trigger generation circuit repeatedly generates a trigger pulse for forming a transmission ultrasonic wave at a predetermined rate frequency fr Hz (period: 1 / fr second). Further, in the delay circuit, a delay time required for focusing the ultrasonic wave into a beam shape for each channel and determining the transmission directivity is given to each trigger pulse. The pulsar circuit applies a drive pulse to the probe 12 at a timing based on the trigger pulse. Further, the ultrasonic transmission unit 20 performs ultrasonic transmission described later based on a control signal from the control unit 31 in the color Doppler imaging processing.

  The ultrasonic receiving unit 21 includes an amplifier circuit, an A / D converter, a delay circuit, an adder, a quadrature detection circuit, and the like (not shown). The amplifier circuit amplifies the echo signal captured via the probe 12 for each channel. The A / D converter converts the amplified analog echo signal into a digital echo signal. The delay circuit determines the reception directivity for the digitally converted echo signal, gives a delay time necessary for performing the reception dynamic focus, and then performs an addition process in the adder. By this addition, the reflection component from the direction corresponding to the reception directivity of the echo signal is emphasized, and a comprehensive beam for ultrasonic transmission / reception is formed by the reception directivity and the transmission directivity. The quadrature detection circuit converts the output signal of the adder into a baseband in-phase signal (I signal: In-phase signal) and a quadrature signal (Q signal: Quadrature-phase signal). The quadrature detection circuit outputs an I signal and a Q signal (IQ signal) as an echo signal to a subsequent processing system. In the quadrature detection circuit, processing for conversion to an RF (Radio Frequency) signal may be executed. Note that the ultrasonic reception unit 21 performs ultrasonic reception described later based on a control signal from the control unit 31 in the color Doppler imaging processing.

  The input buffer 22 is a buffer that temporarily stores an echo signal (IQ signal or RF signal) output from the ultrasonic receiving unit 21. The input buffer 22 is, for example, a FIFO (First-In / First-Out) memory, and temporarily stores IQ signals for several frames (or IQ signals corresponding to several volumes). In addition, when an IQ signal for one frame is newly output from the ultrasound receiving unit 21, the input buffer 22 newly receives an IQ signal corresponding to the oldest frame in time from the ultrasound receiving unit 21. Rewrite to IQ signal.

  The B-mode processing unit 23 receives the echo signal from the input buffer 22, performs logarithmic amplification, envelope detection processing, and the like, and generates data in which the signal intensity is expressed by brightness.

  The color Doppler processing unit 24 executes color Doppler processing using the echo signal received from the input buffer 22 and outputs a power signal and a speed signal.

  The FFT Doppler processing unit 25 performs Fast Fourier Transform using echo signals acquired in the continuous wave Doppler mode, and outputs a spectrum signal.

  The RAW data memory 26 uses the plurality of B mode data received from the B mode processing unit 23 to generate B mode RAW data which is B mode data on a three-dimensional ultrasonic scanning line. The RAW data memory 26 generates blood flow RAW data, which is blood flow data on a three-dimensional ultrasonic scanning line, using a plurality of blood flow data received from the color Doppler unit 24. Note that a spatial smoothing may be performed by inserting a three-dimensional filter after the RAW data memory 26 for the purpose of noise reduction and image connection.

  The volume data generation unit 27 generates B-mode volume data and blood flow volume data by executing RAW-voxel conversion including interpolation processing with consideration of spatial position information.

  The image processing unit 28 includes volume data received from the volume data generation unit 27 or the motion information processing unit 29, volume rendering, multi-planar reconstruction display (MPR: Multi Planar Reconstruction), maximum value projection display (MIP: Maximum Intensity Projection), etc. Predetermined image processing is performed. For the purpose of reducing noise and improving image connection, a two-dimensional filter may be inserted after the image processing unit 28 to perform spatial smoothing.

  The motion information processing unit 29 uses the B-mode volume data or blood flow volume data output from the volume data generation unit 27 to execute various processes related to the tissue tracking imaging method. Further, the motion information processing unit 29 performs processing (ventricular three-dimensional myocardial shape setting support processing) according to a later-described ventricular three-dimensional myocardial shape setting support function in the tissue tracking imaging method. The configuration and operation of the motion information processing unit 29 will be described in detail later.

  The display processing unit 30 executes various types such as dynamic range, brightness (brightness), contrast, γ curve correction, and RGB conversion on various image data generated and processed by the image processing unit 28.

  The control processor 31 has a function as an information processing apparatus (computer) and controls the operation of each component. Further, the control processor 31 controls the motion information processing unit 29 and the like in a ventricular three-dimensional myocardial shape setting support process to be described later.

  The storage unit 32 stores a program for executing the tissue tracking imaging method, a program for realizing a later-described ventricular three-dimensional myocardial shape setting support function, a diagnostic protocol, transmission / reception conditions, and other data groups. Yes. Further, it is also used for storing images in an image memory (not shown) as required. Data in the storage unit 32 can be transferred to an external peripheral device via the interface unit 33.

  The interface unit 33 is an interface related to the input device 13, a network, and a new external storage device (not shown). It is also possible to connect another device to the ultrasonic diagnostic apparatus main body 11 via the interface unit 33. Further, data such as an ultrasonic image obtained by the apparatus, analysis results, and the like can be transferred by the interface unit 33 to another apparatus via a network.

(Tissue tracking imaging)
Next, a tissue tracking imaging method (TTI: Tissue Tracking Imaging), which is a premise of the present embodiment, will be briefly described. In this tissue tracking imaging method, local displacement and strain parameters are imaged while tracking a tissue position accompanying the motion as tissue motion information. According to this technique, an image of distortion or displacement of the local myocardium of the heart can be created and displayed using, for example, a short-axis image, and analysis of temporal changes with respect to the local region of the image output value is supported. Further details of the tissue tracking imaging method are described in, for example, Japanese Patent Application Laid-Open No. 2003-175041.

  Note that this tissue tracking imaging method requires a spatiotemporal distribution image (an image representing a velocity at each position of a diagnosis target tissue) regarding a plurality of time phases. The spatiotemporal distribution image of tissue velocity (hereinafter simply “velocity distribution image”) is subjected to pattern matching processing on a plurality of two-dimensional or three-dimensional tissue images related to a plurality of time phases collected by the B mode or the like. Alternatively, it is obtained by generating from two-dimensional or three-dimensional ultrasonic image data regarding a plurality of time phases collected by the tissue Doppler method. In recent years, this method based on pattern matching processing is generally called a speckle tracking method.

(Exercise information processing unit)
The motion information processing unit 29 executes the processing related to the tissue tracking imaging method described above (particularly, the tissue tracking imaging method using the ventricular three-dimensional myocardial shape setting support function described later).

  FIG. 2 is a block configuration diagram of the motion information processing unit 29. As shown in the figure, the exercise information processing unit 29 includes a first setting unit 290, a second setting unit 292, a ventricular shape setting unit 294, a tracking processing unit 296, and an exercise information generating unit 298.

  The first setting unit 290 performs a blood flow inflow into the ventricle with respect to the volume data related to the heart generated in the volume data generation unit 27 in the three-dimensional myocardial shape setting support process described later 1 part) is set.

  The second setting unit 292 performs a flow (outflow of blood flow from the ventricle with respect to the volume data related to the heart generated in the volume data generation unit 27 in the three-dimensional myocardial shape setting support process described later. 2D) three-dimensional shape is set.

  The ventricular shape setting unit 294 sets the three-dimensional myocardial shape of the ventricle including the first part and the second part in the volume data using the three-dimensional shape of the first part and the three-dimensional shape of the second part.

  The tracking processing unit 296 sets each target (for example, the three-dimensional myocardial shape of the ventricle, the first part axis, the second part axis, etc.) set for the volume data in the reference time phase (for example, the initial time phase). The position is tracked by performing pattern matching processing on a plurality of volume data related to a plurality of time phases, and a velocity distribution image in each time phase is generated.

  The motion information generation unit 298 uses the generated velocity distribution image at each time phase to acquire motion information (for example, strain, strain rate, displacement, speed, twist) at each position of the myocardium. twist), twist rate, etc.).

(3D myocardial shape setting support function of the heart chamber)
Next, the three-dimensional myocardial shape setting support function of the heart chamber included in the ultrasonic diagnostic apparatus 10 will be described. In this time phase estimation process, for example, when the myocardial tissue is imaged by the tissue tracking imaging method, the first part where blood flows in, the second part where blood flows out, and the myocardial region including the heart chamber are set. It is to support. In the following, for the sake of concrete explanation, the “heart chamber” is the “right ventricle”, and the “first portion” is the “tubular structure including a tricuspid valve” for allowing blood to flow into the right ventricle. It is assumed that the “second part” is a “tubular structure including a pulmonary artery valve (outflow part)” for allowing blood to flow out of the right ventricle. However, the purpose is not limited to this example. For example, the “heart chamber” may be “left ventricle”, “right atrium” or “left atrium”, and “first part” or “second part” It may be other than a tubular region.

  FIG. 3 is an example of a flowchart in the case of performing tissue tracking imaging using the three-dimensional myocardial shape setting support function of the ventricle realized by the ultrasonic diagnostic apparatus 1 according to the present embodiment. Hereinafter, processing executed in each step will be described in detail.

[Obtain Volume Data: Step S1]
First, at least a three-dimensional region including the right ventricle is subjected to ultrasonic scanning (scanning by the B mode), and volume data for each time phase is acquired for a predetermined period over, for example, one heartbeat or more. Here, “time phase” or “cardiac time phase” refers to an arbitrary time point (timing) in the periodic motion of the heart.

  In the present embodiment, volume data over a plurality of time phases is acquired in order to exemplify application to a typical tissue tracking imaging method. However, the three-dimensional myocardial shape setting support function of the main ventricle can be realized if there is volume data corresponding to the temporary phase. Therefore, in this step S1, volume data in one time phase corresponding to, for example, end diastole (End-systole) or end systole (End-Diastole) may be acquired as necessary.

[First part setting process: Step S2]
The first setting unit 290 performs blood inflow into the right ventricle with respect to volume data corresponding to a predetermined time phase (for example, an initial time phase) among the acquired volume data corresponding to each time phase. The contour line of the myocardial region of the first part is input using a cross section along the axis of the first part, and a three-dimensional shape approximating the first part is set by interpolation processing. More specifically, it is as follows.

  FIGS. 4A, 4 </ b> B, 5 </ b> A, 5 </ b> B, and 5 </ b> C are diagrams for explaining the first part setting process. When a plurality of volume data over a plurality of time phases are acquired in step S1, the first setting unit 290 performs the first part on the volume data corresponding to the predetermined time phase as shown in FIG. Two long-axis cross sections SA and SB (for example, two orthogonal cross sections) are set along the axis A1 (along the extending direction of the first portion). Here, the “extending direction” means, for example, a straight line connecting the center of the entrance and the center of the exit of the cylindrical inflow path, or a direction along an approximate line. Moreover, in the above description, an example in which “it is along the extending direction of the first part” is shown, but it is parallel, but the angle between the extending direction of the first part is within ± 20 degrees without being restricted to this. It may be.

  Although the two long-axis cross sections SA and SB can be set according to a predetermined algorithm, they may be set or finely adjusted by manual operation. When the two long-axis cross sections SA and SB along the axis A1 of the first part are set, the image processing unit 28 generates the long-axis cross-sectional images SAI and SBI corresponding to the long-axis cross sections SA and SB, respectively. To do. The generated long-axis cross-sectional images SAI and SBI are displayed on the monitor 14 as shown in FIG. 4B, for example.

  The user traces the outline of the myocardial region at the first site (inflow part) via the input device 13 with respect to the two long-axis cross-sectional images SAI and SBI displayed as shown in FIG. For example, contour lines 50 and 51 are set in the long-axis cross-sectional image SAI, and contour lines 52 and 53 are set in the long-axis cross-sectional image SBI.

  As shown in FIG. 5A, the spatial positional relationship between the four contour lines 50, 51, 52, 53 can be clearly grasped as coordinates on the volume data. As shown in FIG. 5B, the first setting unit 290 sets a short-axis section SX1 that intersects the long-axis sections SA and SB, and the short-axis section and four contour lines 50, 51, 52, and 53. The outline of the first part is approximated by an ellipse EL1 using the four points that intersect. Similarly, the first setting unit 290 sets short-axis cross sections SX2, SX3,..., SXn that intersect the long-axis cross sections SA, SB, and each short-axis cross section and four contour lines 50, 51, 52. , 53 are used to approximate the contour of the first part with ellipses EL2, EL3,..., ELn. The first setting unit 290 sets a three-dimensional shape that approximates the first part in the volume data by interpolating the obtained ellipses EL2, EL3,..., ELn. In the above description, “intersect” means one of intersecting, forming an angle of 70 degrees to 110 degrees, and more preferably forming an angle of 90 degrees.

  In the above description, the case where the outline of the myocardial region in the first region is set using the two long-axis cross sections SA and SB is illustrated. However, the present invention is not limited to this example, and the outline of the myocardial region in the first site may be set using three or more long-axis cross sections. In addition, although the two long-axis cross sections SA and SB are two orthogonal cross sections, they are not necessarily orthogonal. Furthermore, the outline of the myocardial region in each long-axis cross-sectional image may be automatically estimated by, for example, the image processing method shown in Non-Patent Document 1.

[Second part setting process: Step S3]
The second setting unit 292 sets the outline of the myocardial region of the second part for performing blood outflow from the right ventricle along the axis of the second part with respect to the volume data corresponding to the predetermined time phase. A cross-sectional image is input, and a three-dimensional shape approximating the second part is set by interpolation processing. More specifically, it is as follows.

  6, FIG. 7 (a), (b), (c) is a figure for demonstrating the setting process of a 2nd site | part. The second setting unit 292 sets the long-axis section SC along the axis A2 of the second part (along the extending direction of the second part) for the volume data corresponding to the predetermined time phase. Although the setting of the long-axis cross section SC can be realized according to a predetermined algorithm, it may be set or finely adjusted by manual operation. When the long-axis section SC along the axis A2 of the second part is set, the image processing unit 28 generates a long-axis section image SCI corresponding to the long-axis section SC. The generated long-axis cross-sectional image SC is displayed on the monitor 14 as shown in FIG. 6, for example. Note that “extending direction”, “along the extending direction”, and the like are as described above.

  The user traces the outline of the myocardial region at the second site (outflow part) via the input device 13 on the long-axis cross-sectional image SCI displayed as shown in FIG. Contour lines 60 and 61 are set.

  As shown in FIG. 7A, the spatial positional relationship between the two contour lines 60 and 61 can be clearly grasped as coordinates on the volume data. As shown in FIG. 7B, the second setting unit 292 sets a short-axis section SY1 that intersects the major-axis section SC, and sets two points where the minor-axis section and the two contour lines 60 and 61 intersect. The contour of the second part is approximated by a circle C1. Similarly, the second setting unit 292 sets short-axis cross sections SY2, SY3,..., SYn that intersect the long-axis cross-section SC, and each short-axis cross-section and the two contour lines 60 and 61 intersect. The contour of the second part is approximated by circles C2, C3,..., Cn using points. The second setting unit 292 sets a three-dimensional shape approximating the second part in the volume data by interpolating the obtained circles C2, C3,..., Cn.

  Here, in the setting of the first part as the inflow part, the ellipse approximation is performed using the two long-axis cross sections SA and SB. However, in the setting of the second part as the outflow part, the single long-axis section SC is used. It was approximated by a circle. This is due to the following reason. In other words, the inflow portion is a tubular structure including a tricuspid valve, but the tricuspid valve is connected to the right atrium, so that the inflow portion has a slightly complicated shape. Therefore, it is desirable to approximate by an elliptical tube rather than a simple tube. On the other hand, in the outflow part, the pulmonary artery valve is connected to the pulmonary artery or blood vessel. Since the blood vessel has a cylindrical shape, the method of this embodiment is also a reasonable approximation. Also, considering the image quality of the ultrasonic image, the outflow part is an acoustic window (the area of the rib that can pass ultrasonic waves without being covered by the lungs) in contrast to the inflow part where sufficient visibility can be secured. It is drawn unclearly due to restrictions. Since the short axis image is significantly affected by the short axis image as in the prior art, it is very difficult to visually recognize the myocardial boundary of the outflow portion. In contrast, the inventors have found that in the long-axis image, the myocardial boundary of the outflow portion is relatively easy to visually check. Therefore, by inputting the contour line of the myocardial boundary using one cross section of the long axis, both the accuracy of approximation and the reduction of the time required for the analysis are compatible.

  As a result of the processing in steps S2 and S3, for example, as shown in FIG. 8, the three-dimensional shape of the first part VI and the three-dimensional shape of the second part VO are respectively set on the volume data.

  Note that the outline of the myocardial region may be automatically estimated by the image processing method shown in Non-Patent Document 1, as with the first setting unit 290. Further, there is no problem even if the order of the first part setting process in step S2 and the second part setting process in step S3 is reversed.

[Setting of three-dimensional myocardial shape of ventricle: step S4]
The ventricular shape setting unit 294 sets the three-dimensional myocardial shape of the ventricle including the first part and the second part in the volume data by using the approximated three-dimensional shape of the first part and the three-dimensional shape of the second part. . As a result, for example, as shown in FIG. 9, the three-dimensional myocardial shape VE of the ventricle including the three-dimensional shape of the first part VI and the three-dimensional shape of the second part VO is set (or extracted).

  In the present embodiment, the oval shape and the circular shape shown in FIG. 10A are shown on the cross-sectional image connected to the ventricle so that the three-dimensional shapes of the inflow portion and the outflow portion are smoothly connected. As shown in FIG. 10 (b), it is deformed according to the shape of the ventricle. However, the present invention is not limited to this example. For example, only one of the inflow portion and the outflow portion may be deformed on the cross-sectional image connected to the ventricle. The shape may be used as it is without being deformed to be connected to the ventricle.

[Myocardial tracking by pattern matching: Step S5]
The tracking processing unit 294 executes, for example, a pattern matching process in time series for volume data corresponding to each other time phase, using the three-dimensional myocardial shape of the ventricle set in the predetermined time phase as an initial shape. Track 3D myocardial shape. Thereby, a three-dimensional myocardial shape of the ventricle is set in each volume data corresponding to a plurality of time phases, and a velocity distribution image in each time phase is generated.

  Further, the tracking processing unit 294 uses the axis of the first part and the axis of the second part in the predetermined time phase as necessary, and uses the volume data corresponding to each other time phase (or some desired number of times). For example, the pattern matching process is executed in time series for the volume data corresponding to the time phase, thereby tracking the axis of the first part and the axis of the second part. Thereby, the axis | shaft of a 1st site | part and the axis | shaft of a 2nd site | part are set in each volume data corresponding to several time phases. By executing the processing of steps S2 and S3 using the axis of the first part and the axis of the second part in each time phase set in this way, the three-dimensional myocardial shape of the ventricle is added to the volume data in each time phase. You may make it set.

[Generation / display of 3D image showing 3D myocardial shape of ventricle: step S6]
The image processing unit 28 displays the three-dimensional myocardial shape of the ventricle including the first part and the second part by executing volume rendering, for example, using each volume data in which the three-dimensional myocardial shape of the ventricle is set. Generate a three-dimensional image. Alternatively, the image processing unit 28 performs MPR processing using each volume data in which the three-dimensional myocardial shape of the ventricle is set, thereby cutting out the heart in an arbitrary cross section and displaying the boundary line where the three-dimensional myocardial boundary intersects. A cross-sectional image is generated. The generated image is displayed in a predetermined form on the monitor 14 after being subjected to predetermined processing in the display processing unit 30.

  In addition, the motion information generation unit 298 generates motion information at each position of the myocardium using the generated velocity distribution image at each time phase. The image processing unit 28 uses the generated motion information at each position of the myocardium to generate a motion information image in which, for example, distortion of the ventricular myocardial region in each time phase is visualized. The generated image is displayed in a predetermined form on the monitor 14 after being subjected to predetermined processing in the display processing unit 30.

(Modification 1)
In the present embodiment, based on the approximated three-dimensional shape of the first part and the second part, the three-dimensional myocardial shape of the ventricle including the first part and the second part is set in the volume data. However, the present invention is not limited to this example. For example, if there is information related to the shape of the ventricle in advance, it may be used. Specifically, when there is a three-dimensional shape that approximates the ventricle by a conventional method or the like, the ventricular shape setting unit 294 firstly connects the ventricle and the first part and the ventricle and the second part smoothly. The configuration may be such that the myocardial boundary between the inflow portion and the outflow portion of the ventricle is generated by deforming the three-dimensional shape of the region and the second region. Further, the ventricle shape setting unit 294 may be configured to use not only a three-dimensional shape but also image information. Information on the shape of the ventricle and the like is stored in, for example, the storage unit 32 or a storage device on the network, and can be acquired at a predetermined timing.

(Modification 2)
In this embodiment, when setting the outline of the myocardial region, the two long-axis cross sections SA and SB are used in the setting of the first part, and the long-axis cross-sections SA and SB are used in the setting of the second part. The case where a different long-axis cross-section SC is used is illustrated. However, the present invention is not limited to this example. For example, the long-axis section SC may be the same (same) section as the long-axis section SA or SB. That is, when there is the second part on the long-axis cross section SA or SB, the second part may be set using the long-axis cross-section SA or SB.

  FIG. 11 shows the myocardial region in the case where the long-axis section SB used for setting the outline of the myocardial region in the first part and the long-axis section SC used for setting the outline of the myocardial region in the second part are the same. It is the figure which illustrated the setting screen of the outline. As shown in the figure, according to the present modification, two cross-sectional images for setting both the outline of the myocardial region at the first site and the outline of the myocardial region at the second site can be provided. . Therefore, the user operation can be further simplified as compared with the case where each contour line is set using three long-axis cross-sectional images.

(effect)
According to the ultrasonic diagnostic apparatus described above, with respect to the outflow portion, in the long-axis cross-sectional image that is relatively easy to visually recognize, the inflow portion having a slightly complicated shape inputs the contour line in two cross sections, and uses this to input an elliptical cylinder. Approximate. On the other hand, for the outflow portion that is simple because of blood vessels and is difficult to visually recognize, a contour line is input in one cross section, and this is approximated by a cylinder. Then, using the approximated three-dimensional shape of the first part and the three-dimensional shape of the second part, the three-dimensional myocardial shape of the ventricle including the first part and the second part is set in the volume data. Therefore, the user can easily and accurately set the myocardial boundary for the ventricle. Further, since the accuracy of setting the myocardial boundary is improved, the time required for analysis and diagnosis can be reduced, and the accuracy of analysis and diagnosis can be improved. Furthermore, it is possible to achieve both reduction of time required for analysis and diagnosis and improvement of accuracy of analysis and diagnosis.

  Note that the present invention is not limited to the above-described embodiment as it is, and can be embodied by modifying the constituent elements without departing from the scope of the invention in the implementation stage. In addition, various inventions can be formed by appropriately combining a plurality of components disclosed in the embodiment. For example, some components may be deleted from all the components shown in the embodiment. Furthermore, constituent elements over different embodiments may be appropriately combined. Specific examples of modifications are as follows.

  (1) The ultrasonic diagnostic apparatus of the above-described embodiment and each modification can be realized by using, for example, a general-purpose computer apparatus as basic hardware. That is, the functions of the above-described units can be realized by causing a processor mounted on the computer device to execute a program. At this time, the ultrasonic diagnostic apparatus may be realized by installing the above program in a computer device in advance, or may be stored in a storage medium such as a CD-ROM or distributed through the network. Then, this program may be realized by appropriately installing it in a computer device. The storage unit described above is realized by appropriately using a memory, a hard disk or a storage medium such as a CD-R, a CD-RW, a DVD-RAM, a DVD-R, or the like that is built in or externally attached to the computer device. be able to.

  (2) In the above embodiment, the case where the three-dimensional myocardial shape is set in the volume data in the initial time phase in the TTI method has been described as a typical example. However, the present invention is not limited to this example, and can be applied to any imaging method as long as it is necessary to set a three-dimensional myocardial shape in volume data.

  (3) In the above embodiment, the ventricular region has been described as an example of the setting target of the three-dimensional myocardial shape. However, the present invention is not limited to this example and can be applied to the right atrium or the left atrium.

  In addition, various inventions can be formed by appropriately combining a plurality of components disclosed in the embodiment. For example, some components may be deleted from all the components shown in the embodiment. Furthermore, constituent elements over different embodiments may be appropriately combined.

DESCRIPTION OF SYMBOLS 1 ... Ultrasonic diagnostic apparatus, 12 ... Ultrasonic probe, 13 ... Input device, 14 ... Monitor, 20 ... Ultrasonic transmission unit, 21 ... Ultrasonic reception unit, 22 ... Input buffer, 23 ... B-mode processing unit, 24 ... Color Doppler processing unit, 25 ... FFT Doppler processing unit, 26 ... RAW data memory, 27 ... Volume data generation unit, 28 ... Image processing unit, 29 ... Motion information processing unit, 30 ... Display processing unit, 31 ... Control processor (CPU) , 32 ... storage unit, 33 ... interface unit, 290 ... first setting unit, 292 ... second setting unit, 294 ... ventricular shape setting unit, 296 ... tracking processing unit, 298 ... exercise information generation unit.

Claims (10)

A data acquisition unit for acquiring volume data based on ultrasonic scanning for a three-dimensional region including at least a part of the heart;
The three-dimensional shape of the first part is acquired based on the outline of the first part in each of a plurality of cross-sectional images that intersect each other along the extending direction of the first part corresponding to the blood inflow route to the heart chamber. An acquisition unit that acquires a three-dimensional shape of the second part based on an outline of the second part in a cross-sectional image along the extending direction of the second part corresponding to the blood outflow path from the heart cavity;
Using the three-dimensional shape indicating the heart chamber and the three-dimensional shapes of the first part and the second part acquired by the acquisition unit, the first part, the second part, and the heart cavity An image generation unit for generating a three-dimensional image showing the shape of at least a part of the myocardium including:
An ultrasonic diagnostic apparatus comprising:   The image generation unit uses the volume data in which the three-dimensional shape indicating the heart chamber and the three-dimensional shapes of the first part and the second part acquired by the acquisition unit are set. The ultrasonic diagnostic apparatus according to claim 1, wherein: The data acquisition unit
Using at least two or more of the cross-sectional images along the extending direction of the first part to set an outline of at least a part of the myocardial region of the first part;
An ellipse is set on each third cross section based on the position where the outline passes through each of a plurality of third cross sections intersecting with the axis along the extending direction of the first part,
Interpolating the plurality of ellipses to obtain a three-dimensional shape of the first part;
The ultrasonic diagnostic apparatus according to claim 1 or 2. The data acquisition unit
Setting a contour line of at least a part of the myocardial region of the second site using the cross-sectional image along the extending direction of the second site;
A circle is set on each of the fourth cross sections based on the position where the outline passes through each of a plurality of fourth cross sections intersecting with the axis along the extending direction of the second portion,
Obtaining a three-dimensional shape of the second part by interpolating the plurality of circles;
The ultrasonic diagnostic apparatus according to claim 1, wherein:   The image generation unit generates a three-dimensional image representing a three-dimensional myocardial shape of the ventricle including the first part and the second part by further using information on the heart chamber prepared in advance. The ultrasonic diagnostic apparatus according to any one of claims 1 to 3.   6. The cross-sectional image along the extending direction of the second part is the same cross-section as any one of a plurality of cross-sectional images along the extending direction of the first part. The ultrasonic diagnostic apparatus according to claim 1. Using the axis along the extending direction of the first part and the axis along the extending direction of the second part in the predetermined time phase, the volume of the first part in the volume data of at least one other time phase is used. A tracking processing unit for tracking an axis along the extending direction and an axis along the extending direction of the second portion;
The data acquisition unit sets the volume data of the at least one other time phase using the plurality of cross-sectional images along the extension direction of the tracked first part, and the set A three-dimensional shape of the first part is acquired based on at least a part of a contour line of the myocardial region of the first part, and the second tracked second volume data is obtained for the at least one other time phase volume data. Set using the plurality of cross-sectional images along the extending direction of the region, and obtain the three-dimensional shape of the second region based on the contour line of at least a part of the myocardial region of the set second region And
The image generation unit uses the three-dimensional shape of the one part and the three-dimensional shape of the second part in the at least one other time phase to obtain the tertiary of the ventricle including the first part and the second part. Generating a three-dimensional image representing the original myocardial shape;
The ultrasonic diagnostic apparatus according to claim 1, wherein: The ventricle is the right ventricle;
The first part is a tubular structure including a tricuspid valve;
The second portion is a tubular structure including a pulmonary valve;
The ultrasonic diagnostic apparatus according to any one of claims 1 to 7, wherein: A storage unit for storing volume data based on ultrasonic scanning for a three-dimensional region including at least a part of the heart;
The three-dimensional shape of the first part is acquired based on the outline of the first part in each of a plurality of cross-sectional images that intersect each other along the extending direction of the first part corresponding to the blood inflow route to the heart chamber. An acquisition unit that acquires a three-dimensional shape of the second part based on an outline of the second part in a cross-sectional image along the extending direction of the second part corresponding to the blood outflow path from the heart cavity;
Using the three-dimensional shape indicating the heart chamber and the three-dimensional shapes of the first part and the second part acquired by the acquisition unit, the first part, the second part, and the heart cavity An image generation unit for generating a three-dimensional image showing the shape of at least a part of the myocardium including:
An ultrasonic image processing apparatus comprising: On the computer,
Using volume data based on ultrasound scanning over a three-dimensional region containing at least part of the heart,
The three-dimensional shape of the first part is acquired based on the outline of the first part in each of a plurality of cross-sectional images that intersect each other along the extending direction of the first part corresponding to the blood inflow route to the heart chamber. An acquisition function for acquiring a three-dimensional shape of the second part based on an outline of the second part in a cross-sectional image along the extending direction of the second part corresponding to the blood outflow path from the heart cavity;
Using the three-dimensional shape indicating the heart chamber and the three-dimensional shapes of the first part and the second part acquired by the acquisition unit, the first part, the second part, and the heart cavity An image generation function for generating a three-dimensional image showing a shape of at least a part of the myocardium including
An ultrasonic image processing program characterized by realizing the above.